ECG SIGNAL ACQUISITION
HARDWARE DESIGN
University of Alabama
ECE Department
BACKGROUND

ECG/EKG (electrocardiogram)
Records the heart's electrical activity:

Heart beat rate

Heart beat rhythm

Heart strength and timing
NOTE: THE LAST SLIDE HAS ALL
REFERENCES THESE SLIDES HAVE
REFERRED TO.
ALL THESE SLIDES COVER THE MAJOR
IDEAS OF ECG SENSOR DESIGN FROM
JOURNAL PAPERS (REFERENCES [1] –
9
[9])
BACKGROUND
ECG works mostly by detecting
and
amplifying
the
tiny
potential changes on the skin
that are caused when the
electrical signal in the heart
muscle is charged and spread
during each heart beat.
This is detected as tiny rises
and falls in the voltage
between two electrodes placed
either side of the heart.
BACKGROUND
 The



heart's electrical system:
Sinoatrial(SA) node
Atrioventricular(AV)
node
His-Purkinje system
BACKGROUND
Schematic representation of
normal ECG
P wave: signal spread from
SA node to make the atria
contract.
P-Q Segment: signal arrives
AV node stay for a instant
to allow the ventricle to
be filled with blood.
Q wave :After the Buddle of
His the signal is divided
into two branches and
run through the septum.
R,S wave: Left and right
ventricle contraction are
marked by the R,S wave.
T wave: ventricle relaxing
ECG SIGNAL

ECG bio-signal typical specifications:
low differential voltage from 0.4 to 3 mV
 high common-mode rejection ratio level
 low frequency range
 high noise

ECG SIGNAL
Artifacts (disturbances) can have many causes.
Common causes are:
 Movement

Sudden movement
Baseline drift
ECG SIGNAL

Electrical interference
From a nearby electrical appliance. A typical
example is a 100 Hz background distortion from
fluorescent lights. To be confused with atrial
fibrillation.
ECG ELECTRODE
Lead
 The signal recorded as the difference between
two potentials on the body surface is called an
"ECG lead". Each lead is said to look at the
heart from a different angle.

ELECTRODE

Lead position
Lead III
Lead 12
ECG ELECTRODE
A typical surface electrode used
for ECG recording is made of
Ag/AgCl, as shown on right
Figure . The disposable electrodes
are attached to the patients’ skin
and can be easily removed.
① Limb Leads (Bipolar)
② Chest Leads (Unipolar)
③ Augmented Limb Leads
(Unipolar)
Wet, dry and insulating…
DESIGN(1)

A 0.5-uVrms 12-uW Wirelessly Powered
Patch-Type Healthcare Sensor [1]

Thick-film electrodes

Fabric inductor

W-BSN controller

Desired Circuit Design (LDO , NCA, PGA,
ADC)
DESIGN(1)
 Advantages:

Long-term continuous monitoring, comfortable
without skin irritation

Wireless powered without battery through
fabric inductor coupling is realized.

Low electrode referred noise by NCA

Small IC size (2.6 mm2 )

Convenience and Safety
DESIGN(1)
 System
Architecture:
A. Controller on chest
band:
12 x 4 inductor array
and W-BSN controller.
sensors are attached
at arbitrary locations.
automatically finds
the locations and
activates each sensor
by self-configuration
DESIGN(1)
 System
Architecture:
B. Wireless powered Sensor:
Two dry electrodes
Sensor chip
P-FCB inductors
Adhesive bandage
Take the power overhead from the
sensors, moving it to the relatively
power-sufficient health monitoring
chest band.
DESIGN(1)
 Requirements:
•
•
•
Sensor IC must consume power in total of
less than 20 uW.
The noise contribution of the sensor readout
front-end must be less than 1 uVrms.
The contact impedance and the motion
artifacts of the dry fabric electrode must be
minimized
DESIGN(1)
Electrode Design:
Wet electrode: uncomfortable, good
conduction, short time
Plaster electrode:
Stiff, uncomfortable, motion
artifacts
Fabric electrode:
Soft, comfortable, long term
A silver paste is screen printed
directly on a fabric, a stainless
steel powder with grain size of
100 um is added on top of the
silver paste.
DESIGN(1)
 Noise
and Artifacts
A. Electrode Noise:
B. Motion Artifacts:
DESIGN(1)
 System
Architecture:
DESIGN(1)
A.
LDO Regulator
Generated voltage(VDD) is regulated by an LDO
regulator to create an internal silent supply voltage
(VDDR) of 1.7 V, and it is dispatched to the NCA, PGA
and ADC.
DESIGN(1)
B. NCA (nested chopping amplifier)

Chopper amplifier
A chopper amplifier is a type
of amplifier that exhibits
precise outputs and low noise.
Reduces the offset from
part to part.
Reduces the offset over
time
Reduces the offset over
temperature.
Reduces offset over
common mode voltage.
DESIGN(1)
B. NCA (nested chopping amplifier)

Nested Chopping amplifier
A LPF generates a residual offset
proportional to its chopping frequency,
and it may raise the in-band noise power.
Another low-frequency chopper switch is
introduced, enclosing the high-frequency
chopped amplifier.
The inner HF (10 kHz) chopped amplifier
mitigates the 1/f and dc offset drift while
the outer low-frequency (625 Hz) chopper
suppresses the residual offset down to 24
dB.
DESIGN(1)
C. PGA
Different magnitudes of the vital signals with different
bandwidth are matched by adjusting Cin and Cf.
DESIGN(1)
D. Folded 10-b SAR ADC
Utilized with capacitive DAC.
Two internally folded 5-b CDAC
for power efficiency.
Upper& Lower
94% of the CDAC size reduction
It relaxes the power budget of
the ADC driver by
36%
DESIGN(1)
 Implementation

& Results[1]
Chip micrograph and its power breakdown
DESIGN(1)
 Implementation
& Results[1]
Measured ECG waveforms by the proposed wirelessly
powered patch-type healthcare sensor.
DESIGN(1)

Conclusion:

A wirelessly powered wearable healthcare sensor is
presented.

A pair of dry fabric electrodes with stainless steel
powder on to ensure stable contact.


The NCA reduces electrode referred noise down to 0.5
uVrms while boosting its CMRR to greater than 100
dB.
A 9-b ECG recording while consuming only 12-uW
power supplied through fabric inductor coupling.
DESIGN(2)







Uncontacted Doppler Radar System for
Heart and Respiratory Rate Measurements
[2][9]
Introduction
Principle
Implementation
System Architecture
Results
Conclusion
DESIGN(2)



Clip-on wireless ECG for ambulatory cardiac
monitoring design[34]
Measure heart movement rather than electrical
activity is a complementary to ECG
Microwave doppler radar detection
outgoing beam + Doppler-shifted reflected beam
= low frequency signal
(physical motion of the heart)
DESIGN(2)
Microwave oscillator(2.45G)
 Microstrip Transformer
(electrically isolate the
oscillator circuit and also
impedance match to the antenna. )
 Microstrip Patch edge-fed Antenna
 Diode Mixer

DESIGN(2)
Low-pass filter
 Microcontroller(8 bit)
 Wireless Link
2.48G IEEE802.15.4
 Battery and Power(30mw)

DESIGN(2)

System Architecture:
Block diagram of radar system
DESIGN(2)
The radio transceiver is on the custom radar chip,
and a circulator isolates the RF output from the
RF input.
 A single patch antenna is used for both
transmitting and receiving.
 Each baseband channel uses an instrumentation
amplifier for single-to-differential conversion, has
a dc block and gain stage followed by an antialiasing low-pass filter.
 The signals are the then digitized and processed
with a PC with custom MATLAB signal
processing software.

DESIGN(2)

Results:
Heart and respiration signatures
a. the heart motion
signature obtained with
the Doppler radar
system
b. respiration motion
signature obtained with
the Doppler radar,
c.ECG
d. heart motion trace
obtained with the
respiratory effort
belts
DESIGN(2)

Results:
The dotted line is the rate
obtained with the control (ECG
or respiratory effort belts) and
the solid line is that obtained
with the Doppler
radar system.
DESIGN(2)





Conclusion:
Comparison with ECG
Similar to ECG but not
a substitute result
Different for different
persons
However, it may be an interesting portable and
lower cost alternative to M-mode echocardiography
for monitoring of certain types of heart failure
associated with heart mechanics, such as
depressed systolic function, akinesia and fibrillation.
DESIGN (3)








A 60 uW60 nV/ Hz Readout Front-End for
Portable Biopotential Acquisition Systems
[3]
Introduction
Readout Front-end Architecture
AC Coupled Chopped Instrumentation Amplifier
Chopping Spike Filter (CSF)
Programmable Gain Stage
Results
Conclusion
DESIGN (3)
 Introduction



Common biopotential signals: EEG, ECG,EMG
Demand for low-power, small-size, and
ambulatory biopotential acquisition systems.
Comfortable and invisible to eye with long-term
power autonomy, high signal quality, and
configurability for different biopotential signals.
DESIGN (3)
 Introduction
Frequency and amplitude characteristics
of biopotential signals
A.
1/f noise
common-mode
interference
electrode offset
B.
high CMRR
low-noise
HPF
configurable
gain and filter
DESIGN (3)
 Readout
Front-end Architecture
front-end for the acquisition of EEG,
ECG, and EMG signals
DESIGN (3)
 AC
Coupled Chopped
Instrumentation Amplifier
Neither three-opamp IA nor SC IA is
convenient for low-power and low-noise
front-ends.
DESIGN (3)
 AC
Coupled Chopped
Instrumentation Amplifier
ACCIA implementation that can
eliminate the 1/f noise, while filtering the
DEO and the IA offset.
DESIGN (3)
 AC
Coupled Chopped
Instrumentation Amplifier
 Current Feedback Instrumentation
Amplifier


AC coupling filters the DEO, chopping
improves the CMRR and filters the 1/f
noise of the current feed-back IA.
chopping spikes generated at the output
DESIGN (3)
 AC
Coupled Chopped
Instrumentation Amplifier
Complete schematic of the current
feedback IA
DESIGN (3)
 Chopping
Spike Filter (CSF)
To filter chopping spikes
Effect of T&H operation on
the output noise of the IA
DESIGN (3)
 Programmable

Gain Stage
For different signals
Schematic of the VGA. Gain is set by the variable
capacitor bank switches and low-pass cut-off frequency is
set by the BW select switches.
DESIGN (3)
 Results
Die micrograph
DESIGN (3)
 Results
Extracted biopotential signals
DESIGN (3)





Conclusion
A
readout
front-end
with
configurable
characteristics for EEG, ECG and EMG signals is
presented.
Combination of the AC-coupled chopping
technique with the low-power current feedback
IA achieves more than 120 dB CMRR and 57 nV/
Hz input-referred noise density, while consuming
only 11.1 uA from 3 V.
Chopping spike filter stage completely filters the
chopping spike components.
Portable/wearable
DESIGN(4)

Novel dry electrodes for ECG monitoring[4]
Journal of Physiological Measurement

Abstract
Outline
Introduction
Biomedical Basics
Novel dry and capacitive electrodes
Materials and methods
Results
Summary







ABSTRACT

Two novel dry bioelectrodes (conductive &
capacitive) for biopotential monitoring:
development, fabrication and characterization;
Improve the applicability of dry electrodes in
ambulant recording of ECG by reducing motion
artifacts and the contact impedance to the skin;
 Exhibit equivalent and superior contact impedances
and biosignals;
 Integrate a passive filter network into the new
electrodes to suppress slow offset fluctuation of the
ECG signal;

OUTLINE
Introduction
 Biomedical basics
 Novel dry and capacitive electrodes

Reduction of contact impedance
 Reduction of motion artifacts
 Dry electrodes as a passive filter network


Materials and methods
Electrode types
 Characterization methods

Results and discussion
 Summary and outlook

INTRODUCTION
Increased costs for health care.
 A challenge: to develop new OR to improve by
decreasing the costs?



Microsystem technologies => miniaturized and
innovative medical systems => increase the patient
comfort considerably
Cardiovascular diseases! Main cause of death!!!
An early recognition of symptoms help.
 Long-term recording of ECG is desirable, but limited
by electrode performance (only a few days).

BIOMEDICAL BASICS
- SKIN–GEL–ELECTRODE INTERFACE
Ion currents have to be converted to electron currents with
the electrode as the transducer.

The skin impairs the
transfer from ions in the
tissue to electrons in the
electrode.


The capacitance of this layer
is poorly defined and
unstable.
The electrical transducer
comprises the resistance of
the electrolytic gel and the
double layer at the
electrode–electrolyte
interface, as well as the
half-cell potentials at both
electrolyte interfaces.
BIOMEDICAL BASICS
- AG/AGCL GEL, DRY AND CAPACITIVE ELECTRODES

Ag/AgCl gel electrode
weakly polarized;
 introduce very low ohmic impedances;
 limited shelf life and are not reusable;


Dry electrode
partly polarized;
 introduce a parallel circuit of an ohmic and a capacitive
impedance;


Capacitive electrode
perfectly polarized;
 introduce a capacitor;

Limited long-term performance improvement by dry and
capacitive electrode.
NOVEL DRY AND CAPACITIVE
ELECTRODES
Adapt to the skin topography;
 Guarantee small relative motion of the skin to
the electrode;

(1)
NOVEL DRY AND CAPACITIVE

Enlarge the contact area by skin adaptive electrode,
which is soft enough to adapt the geometry of the
hair;
Reduction of motion artifacts


(2)
Reduction of contact impedance


ELECTRODES
Maintain the contact even under motion by a soft
electrode;
Dry electrodes as a passive filter network

Suppress fluctuations by a high-pass filter;
MATERIALS AND METHODS
- ELECTRODE TYPES
1)
2)
3)
4)
Ag/AgCl gel electrode of type ARBO H92SG;
Dry silver electrodes (dry Ag) with a diameter of
2 cm were cut from a 0.3 mm thin silver foil;
Electrodes 2 cm in diameter were punched out
of an electrically conductive foam. They were
coated with a silver layer 400 nm thick on all
surfaces. A 100 nm layer of titanium was used
as an adhesion layer;
Capacitive electrodes (SiO2) were fabricated on
silicon with a thermally grown silicon dioxide as
the dielectric layer;
MATERIALS AND METHODS
- CHARACTERIZATION METHODS (1)

Impedance spectroscopy.


Motion artifacts.


The electrode–skin contact impedance was analyzed
by a computer-controlled HP4192A impedance
analyzer.
The motion artifacts were evaluated from ECGs
taken with a longterm ECG recorder, the
CardioLight Smart Reader.
Minimum distance for electrodes.

Two electrodes were placed next to each other as
close as 1 cm right under the left nipple.
MATERIALS AND METHODS

Passive filtering.
- CHARACTERIZATION METHODS (2)

The transfer function was measured in a two-port
measurement setup.

To eliminate the 50 Hz noise, a shielded measurement
setup and symmetric input impedance at an amplifier with
high common mode rejection is necessary.
RESULTS AND DISCUSSION (1)
RESULTS AND DISCUSSION (2)
RESULTS AND DISCUSSION (3)
RESULTS AND DISCUSSION (4)
SUMMARY AND OUTLOOK



The new dry and capacitive electrodes avoid the
shortcomings of standard Ag/AgCl gel electrodes.
Rigid silver plates, silver plates coated with silver
chloride, Ag-coated conductive polymer foam soft
electrodes, and capacitive SiO2–Si electrodes were
designed, fabricated and characterized with the
objective of improving the contact on hairy skin to
reduce the electrode impedance, to diminish motion
artifacts and to passively filter zero-line fluctuations.
Future work will concentrate on the development of a
soft capacitive electrode to combine the advantages of
both new types of electrodes for a long-term ECG
system, which is convenient with respect to all
relevant electrode properties.
DESIGN(5)










3.9 mW 25-Electrode Reconfigured Sensor[5]
Introduction
Electrode design
System Architecture
REIA
Band switched filter
Remote controller
Low duty cycle transmitter
Implementation and results
Conclusion
DESIGN(5)






Introduction
A low power highly sensitive Thoracic Impedance
Variance (TIV) and Electrocardiogram (ECG)
monitoring SoC.
Multi-application integrated together
TIV requires high impedance detection sensitivity
The low noise requirements
Low power consumption for wearable
DESIGN(5)

Electrode Design:
Tightly attached to the chest to cover
the area of the heart
Compact poultice-like plaster sensor (15
cm* 15 cm 4-layer patch)
Wearable low cost cardiac healthcare
16 different sites across the heart to
enable the optimal sensing point
DESIGN(5)

Electrode Design
25 electrodes array
d(reconfigurable)
Cm-range inductively
coupled power switch
A thin flexible battery of 1.5
V with 30 mAh capacity
Fabric broad
thickness<<2mm
DESIGN(5)
ECG the electrode-skin contact impedance is less
than 120 k at frequencies below1 kHz
 sub-period 1:
ECG (Mode 0) is measured using 8 electrodes in
direction 1

DESIGN(5)

sub-periods 2:
ECG (Mode 0) is measured using 8 electrodes in
direction 0
The optimal sensing point to be selected
DESIGN(5)

1)
2)
3)
4)
5)
System Architecture SoC(5mm*5mm)
a System Start-up Module (SSM)
four Reconfigurable Electrode sensor Front
Ends (RE-FE)
DSCG(Differential Sinusoidal Current
Generator
a digital module
a duty-cycled Body-Channel Transceiver(5%)
DESIGN(5)
Reconfigurable electrode instrumentation
amplifier (REIA)
 Enables reconfigurable electrode operation
 Four switches (SE0–SE3) to time-multiplexed
operation in ECG
detection mode
 noise advantages
 current efficiency
 Gain=R2/R1

DESIGN(5)






Band switched filter
dual-mode operation to selectively amplify ECG
signal
CH +pseudo-resistorhigh pass (0.4Hz)
AC couplingreject
DC offset
C2,R2 LPF (1.1kHz)
PGA minimize the
degradation of SNR
DESIGN(5)
Post processing analog readout signal
path
DESIGN(5)
Remote controller
 remote 8 b ID check
Step 1: remote controller in the base station
provides a continuous wave at 13.56 MHz
Step 2: CMOS rectifier in the SSM generates
Power-on-Reset (PoR) trigger signa
Step 3: transmits an
encoded ID packet
Step 4: decodes
the data packet and
verifiers its ID

DESIGN(5)
PI Decoder
Each symbol of the PIE envelope starts with
’0’ and finishes with ’1’ to separate each symbol
REF as a threshold signal is created by
charging a 4 pF MIM capacitor (2C)

DESIGN(5)

Low duty transceiver
FSK BCT
 5 MHz gives a
data rate of 1 Mbps
 Buffered
 2.3 mW
 %5 duty cycle
DESIGN (5)
 Implementation
& results
Measured gain curve for dualband operation of REIA
Measured TIV and ECG
waveforms
DESIGN (5)
 Conclusion:




A low power, high resolution TIV and ECG monitoring SoC
is designed for wearable.
TIV detection is possible with a high detection sensitivity.
high quality balanced sinusoidal current source and
reconfigurable high CMRR readout electronics are utilized.
Low duty BCT to achieve low power consumption and low
cost
DESIGN(6)







Power-Efficient Cross-Correlation Beat
Detection in Electrocardiogram Analysis
Using Bitstreams [6]
Introduction
Heartbeat Detection
Single-Chip Cross-Correlator
Implementation
Measurement Results
Conclusion
DESIGN(6)





Introduction
The benefit of adopting specialized silicon systems
forminimal size and power consumption in BSN
applications is evident.
Long-term ECG observation sensor worn during
normal activity and should not interfere with normal
lifestyle to catch some typical diseases.
A novel single-chip cross-correlator is proposed for
ECG analyses.
“Smart” ECG electrode with embedded heart-beat
detection
DESIGN(6)
 Heartbeat
Detection
Beat detection involves
identifying all cardiac
cycles in ECG recordings
and locating each
identifiable w avef orm
component within a cycle.
P, QRS, T, Timing…

Trade-off between the computational efficiency
and detection quality.
DESIGN(6)
 Heartbeat

1.
2.
3.
4.

Detection
Multicomponent-Based Heartbeat Detection
Three templates were used to search the wave
isolation.
Locate the QRS complex by cross-correlating the
QRS template with the ECG signal
Repeat with the P, T wave templates.
The threshold value is established during a prelearning phase and can be adjusted.
Computational complexity requires power-efficient
implementations.
DESIGN(6)

Single-Chip Cross-Correlator
Multiply elements from template and input over
a window of lengh n.
The computation methods should be considered
for the power saving.
DESIGN(6)

A.
B.
C.
Single-Chip Cross-Correlator
Bitstream Representation
Perform cross-correlation by processing
bitstream.
Bitstream Conversion
binary-to-bitstream by interpolation filter and
sigma-delta modulator, CIS filter, low OSR
Bitstream Operations
Use simple XNOR , asynchronous counter
design, bubble register, thermometer coded
DESIGN(6)

Single-Chip Cross-Correlator
D. Bitstream Cross-Correlation
Computed directly on bitstream coded signals.
 The template is shifted in directly as a bitstream
coded sequence of up to 1024 bits in a template
register.
 Incoming bitstream signal is shifted through the
correlation register.
 Multiplied by XNOR gates at the start of every clock
cycle.
 Bubble register is loaded with the results for
asynchronous sorting.

DESIGN(6)

Implementation
1x1 mm
Delta-sigma converter
1024-bits crosscorelator
STMicro 90-nm Tech
Chip layout
DESIGN(6)

Implementation
Asynchronous bubble register
diagram of the implemented chip
DESIGN(6)

Measurement Results
(a) QRS template. (b) T template
Cross-correlation results for the QRS
DESIGN(6)




Conclusion
Presented a novel bitstream
-based single-chip running
cross-correlator.
Compact and power-efficient
Reduce communication demands and power
consumption.
DESIGN(7)

A Wearable Health Care System Based on
Knitted Integrated Sensors[7]
Introduction
 Wealthy system
 Wealthy functions
 Materials and Methods
 Results
 Conclusion

DESIGN(7)





Introduction
Need for renovation in our health managing
system.
Comfortable sensing interface, easy to use and
easy to
Textile customize embedded in clothing items
WEALTHY system, conductive and piezoresistive
yarns.
DESIGN(7)




Wealthy system
Strain fabric sensors based on piezoresistive
yarns, fabric electrodes realized with metal-based
yarns.
In the sensitive garment
Continuous monitoring
DESIGN(7)

Wealthy functions

Signal sensing

Signal conditioning

Signal processing

Data transmission
DESIGN(7)

Materials and Methods
A.
Fabric Electrodes
B.
Fabric Piezoresistive Sensor
C.
Impedance Pneumography
D.
Connections
E.
Garment Model and Realization
F.
Washability and Reusability
DESIGN(7)

Results
Signals in basal condition, D1, D2, D3
Einthoven leads I, II, III. V2,V5: standard
precordial leads V2 and V5. Th-R, Ab-R:
respiration sensors in thoracic and
abdominal positions, respectively. Sh-M,
Eb-M:movement sensors on the left
shoulder and elbow, respectively.
Detail of ECG signals during abduction–
adduction of the left shoulder.
DESIGN(7)

Results
Comparison of V2 and V5 precordial leads
acquired with fabric and standard electrodes
Comparison of precordial V2 and V5 ECG
signals obtained with subject walking on the
spot with standard and fabric electrodes.
DESIGN(7)

Conclusion
The most innovative characteristic of the WEALTHY system
consists of the use of conductive and piezoresistive materials
in the form of fibers and yarns.
 These new integrated knitted systems enable applications


The possibility of simultaneously recording different signals

Use of standard textile to realize the sensing elements

possible to perform normal daily activities while the clinical
status is monitored
DESIGN(8)

ECG Recording on a Bed During Sleep
Without Direct Skin-Contact[8]
Introduction
 Methodology
 Experiment Setup
 Results
 Discussion
 Conclusion

DESIGN(8)


Introduction
An electrocardiogram (ECG) measurement
during sleep
 long-term
 easy home usage
 nonintrusive daily ECG monitoring




Indirect contact (IDC) electrocardiogram(ECG)
measurement method (IDC-ECG).
Maintaining contact
Reduce skin irritation
DESIGN(8)

Methodology

Insulated electrodes

An array of active
electrodes

Ground conductive textile

Mattress cover and
pajamas clothes
DESIGN(8)

Methodology
A. Active Electrodes

electrode face,
preamp, and shield.

high-input
impedance amplifier

shield to prevent noise
DESIGN(8)

Methodology
B. Frequency Response of the Active Electrode
OPA124
DESIGN(8)

Methodology
C. ECG Measurement by Electrode Array
D. Indirect-Contact Ground

Requires a reference
Large conductive textile laid on
the lower area of the bed
 compensated for the high impedance
per unit area

DESIGN(8)

Experiment Setup
A. Active Electrode
B. Mattress Assembly
C. Electronics and Data
Acquisition
D. ECG With Ag-AgCl
Electrodes for
Comparison
DESIGN(8)

Results
(a) supine position; (b) on right side; (c) on left side; (d) supine position movement.
DESIGN(8)

Results
Outputs obtained from two of the eight electrodes over a 6-h sleep period
DESIGN(8)




Discussion
Variation in
impedance between
the electrodes and the body and the variation in the whole
body potential due to triboelectricity.
------- cotton produces the least motion artifacts.
Hard to discriminate ECG from most of the large artifacts.
Used for diagnosis in a restricted area or as an auxiliary
method.
DESIGN(8)


Conclusion
An ECG was recorded with distinct R-peaks during
sleep, regardless of body position and location on the
bed.

The waveforms varied according to the contact
condition and position.

Further study on analyzing the waveform is needed
for the motion artifacts.

Shows the feasibility of using IDC-ECG for long-term
daily ECG monitoring during sleep with minimal
intrusion.
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